Low turbulence fluid management system for endoscopic procedures

ABSTRACT

A system and a method for distending a body tissue cavity of a subject by continuous flow irrigation by using two positive displacement pumps, such as peristaltic pumps, one pump on the inflow side and another pump on the outflow side, such that the amplitude of the pressure pulsations created by the positive displacement pumps inside the tissue cavity is substantially dampened to almost negligible levels. The present invention also provides a method of reducing the frequency of the said pressure pulsations. The present invention also provides a method for accurately determining the rate of fluid loss, into the subject&#39;s body system, during any endoscopic procedure without utilizing any deficit weight or fluid volume calculation, the same being accomplished by using two fluid flow rate sensors.

FIELD OF INVENTION

The present invention relates to a system for distending body tissue cavities of subjects utilizing continuous flow irrigation during endoscopic procedures. The system and the methods of the present invention described above can be used in any endoscopic procedure requiring continuous flow irrigation few examples of such endoscopic procedures being hysteroscopic surgery, arthroscopic surgery, trans uretheral surgery (TURP), endoscopic surgery of the brain and endoscopic surgery of the spine. The proposed invention can also have certain useful non medical applications.

BACKGROUND OF THE INVENTION

Endoscopic surgery is becoming increasingly popular because of the following reasons:

-   (a) it is a minimally invasive form of surgery, -   (b) it avoids large incisions over the skin and muscle, -   (c) it is associated with less pain, -   (d) there is a relatively less requirement of blood transfusions and -   (e) the patients can return back to normal work relatively early     with minimal loss of working days.

While in the corresponding open conventional surgeries a relatively large body part consisting of skin and muscle needs to be cut in order to gain access to an underlying body tissue cavity, in endoscopic surgery instead of cutting body structures like skin and muscle an endoscope is introduced into the body cavity via the natural opening of a cavity, if such exists, or alternatively a minute hole is made in the wall of the cavity through which the endoscope is introduced to visualize the interior of the body tissue cavity and to perform major or minor endoscopic surgical procedures. For this reason endoscopic surgery is also sometimes called ‘key hole’ or ‘minimal access surgery’. Besides reducing the pain associated with surgery, endoscopic surgery also helps in reducing the medical expenses.

Endoscopic Surgery is Primarily Related to a Tissue Cavity:

All endoscopic surgeries are carried out on a existing body cavity which is distended or ‘ballooned up’ by a suitable distending apparatus which permits the inner lining of the said tissue cavity to be visualized by the help of an endoscope. Though multiple endoscopic procedures have become established as the preferred surgical modality but still there is immense scope of increasing the safety and efficiency of the such existing endoscopic procedures by improving upon the existing techniques and apparatus used for distending body tissue cavities. Hysteroscopy, arthroscopy, TURP (transuretheral resection of the prostate), endoscopic surgery of the brain and endoscopic surgery of the spine are few of the routinely performed endoscopic procedures and the organs related to such surgeries being uterus, human joints, bladder, brain and the spine respectively. The list of endoscopic surgeries is long, ever increasing and there is hardly any body organ or organ system to which the benefits of endoscopy have not been extended.

Tissue Cavitiy is Initially Collapsed in its Natural State:

In the natural state tissue cavities are collapsed structures and the cavity walls are in apposition with each other as if kissing each other. Thus if an endoscope is introduced in such a collapsed cavity no endoscopic visualization is possible unless the cavity is ballooned up by filling it with a transparent fluid or a gas. Such ballooning of a tissue cavity is technically termed as ‘cavity distension’. No endoscopic procedure can be performed without an efficient cavity distending system and no endoscopic procedure should be attempted without a safe distending system because unsafe tissue cavity distending means can lead to extreme human morbidity and even the death of a patient and such grim realities shall be discussed in the later sections of this manuscript. Cavity distension provides both endoscopic visualization and mechanical distension which is necessary for the movement of endoscopic instruments.

Continuous Flow Irrigation:

In the present invention, the Inventors are focused on a system for distending body tissue cavities for those endoscopic procedures in which the cavity needs to be distended by utilizing continuous flow irrigation only. Here, the term ‘continuous flow irrigation’ means that fluid simultaneously enters and escapes from a tissue cavity via separate entry and exit points, as a result of which a positive fluid pressure is created inside the tissue cavity which distends the cavity.

The Need for Continuous Flow Irrigation:

Any tissue cavity can be easily distended in a ‘static manner’ by simply pushing fluid via a single inflow tube inserted into the cavity and in this manner a desired cavity pressure can be developed and also maintained. For example, a cavity can be distended by pressing on the piston of a simple syringe filled with fluid with the outlet end of the syringe being connected to the cavity by a tube. Alternatively a fluid filled bottle may be elevated to a suitable height and under the influence of gravity fluid from such bottle may be allowed to enter the cavity via a tube connecting the said bottle to the cavity and in this manner a desired static pressure can be developed and also maintained. Though it is very easy to achieve distension by the said static manner, it is not a practical solution because blood and tissue debris which are invariably released from the fragile cavity inner lining mix with the distending fluid and endoscopic vision gets clouded within a few seconds or a few minutes. Thus continuous flow irrigation is needed to constantly wash away blood and tissue debris in order to maintain constant clear endoscopic vision.

Cavity Pressure and Cavity Flow Rate:

It is obvious that cavity fluid pressure and the flow rate through the cavity are the two basic parameters associated with all continuous flow irrigation systems.

An Efficient Distending System:

The Inventors believe that an efficient distending system is the one which provides a predictably continuous clear visualization and a predictably stable mechanical stabilization of the cavity walls. In order to achieve this the Inventors believe that a suitable stable constant precise cavity pressure and a suitable stable precise cavity flow rate have to be created and maintained in a predictable and controlled manner. The cavity pressure should be adequate so that vision is not clouded by oozing of blood and enough mechanical separation of the cavity walls occurs to allow the movement of the endoscope. Similarly, the cavity flow rate should be adequate enough to constantly wash away blood and tissue debris in order to allow clear vision. Many prior systems utilize a peristaltic pump over the inflow and or the outflow side and these peristaltic pumps create pressure pulsations which are then transmitted to the tissue cavity. Such pressure pulsations are undesirable and the main aim of the present invention is to dampen such pressure pulsations.

A Safe Distending System:

An efficient distending system as explained in the previous paragraph need not also be a safe distending system. In this regard, the Inventors would like to highlight that if the cavity pressure rises above the prescribed safe limits excessive fluid intravasation may occur or the cavity may even burst. Fluid intravasation is a process by which the irrigation fluid enters into the patient's body system through the cavity walls and may cause significant danger to the patient's life including death. Thus a safe distending system is one which prevents or minimizes fluid intravasation and allows the surgeon to accurately know the instantaneous real time rate of fluid intravasation into the patient's body system.

No Prior Art is Absolutely Safe:

Many different types of uterine distending systems are known and are being commercially marketed by many different companies but none of these systems can be considered to be absolutely safe for the patient. This fact has been clearly stated in the ‘Hysteroscopic Fluid Monitoring Guidelines proposed by the Ad Hoc Committee on Hysteroscopic Fluid Guidelines of the American Association of Gynecologic Laproscopists February 2000 (Loffler F D, Bradley L D, Brill A I et al: Hysteroscopic fluid monitoring guidelines. The journal of the Americal Association of Gynecologic Laproscopists 7(1): 167-168, 1994) where the authors clearly and explicitly state “fluid pumps for low-viscosity media are a convenience and do not guarantee safety”. The present invention aims at providing a distending system which is both safer and more efficient in comparison to all the prior art systems.

Basic Physics of Cavity Distension:

Although, a person skilled in the art may know it, the Inventors would like to provide a brief description of the basic physics of cavity distension. Filling the tissue cavity with fluid enables distension of the same. Initially more fluid is pumped in than the amount which is extracted from the cavity and ultimately the inflow rate is fixed at a level where a somewhat desired cavity pressure and distension is achieved. It may be possible to accurately maintain the desired pressure and distension in the case of a rigid cavity, for example a cavity made of steel.

However, the body tissue cavities are not rigid because they are distensible and also have some element of elasticity. Thus a distended tissue cavity in its attempt to constantly revert back to its natural collapsed state reacts by exhibiting physiological contractions of the cavity wall which generally leads to variations in the cavity pressure which ultimately culminates in irregular movement excursions of the cavity walls. In a static system the said movement excursions may be so minute that they may even go unnoticed. However in a dynamic system such that being created during an endoscopic procedure, the said physiological cavity wall contractions may cause the cavity to expel out its entire fluid content thus leading to a surgically dangerous large magnitude movement excursion of the cavity wall. Because of these reasons it is extremely difficult to maintain the cavity pressure and cavity distension in a predictably stable fashion.

Further, the inflow tube, the out flow tube and the endoscope also invariably move and shake during surgery which leads to variations in fluid flow resistance which is also manifested in the form of variations in the cavity pressure. The cavity pressure variations occurring as a result of cavity wall contractions and the mechanical movement of the tubes and the endoscope tend to occur again even if they are corrected once because it is impossible to prevent the physiological cavity wall contractions and the mechanical movements of the irrigation circuit. Thus, the said cavity pressure variations shall continue to occur even after multiple repeated corrections.

Thus, till date the surgeon was only left with two options, either to ignore the said cavity pressure variations by not correcting them, or to externally and actively correct such pressure variations. The Inventors have noticed that any attempt to externally and actively correct the said cavity pressure variations leads to an undesirable turbulence inside the cavity and also tends to amplify the resultant movement excursions of the cavity walls. Thus there is a grave need to provide a system which can maintain an almost constant and stable cavity pressure even in the presence of the said physiological cavity contractions and the mechanical movements in the irrigation circuit.

Brief Description of an Endoscope:

Prior to describing the basic layout of a continuous flow irrigation system the basic structure of an ‘endoscope’ needs to be described. Endoscope is a cylindrical tube having an outer diameter ranging between 3 to 9 mm approximately. A typical endoscope has four channels. One channel is meant to pass a fibereoptic telescope while endoscopic instruments are negotiated through a second instrument channel. A third channel also known as the inflow channel is used for pushing irrigation fluid into a tissue cavity, the proximal end of this channel ending in a metal adaptor known as the inflow port while the distal end of this inflow channel opens near the tip of the endoscope. The inflow port is connectable to an inflow tube which carries sterile irrigation fluid from a fluid source reservoir. A fourth channel also known as the out flow channel is meant for extracting waste fluid out of the cavity, the proximal end of this channel ending in a metal adaptor known as the outflow port while the distal end of this outflow channel opens near the tip of the endoscope. The outflow port is connectable with an outflow tube which transports the waste fluid from the cavity to a suitable waste fluid collecting reservoir. A set of fiber optic bundles contained inside the telescope transmit light energy produced by an external light source. This light energy illuminates the walls of the tissue cavity. The image thus formed is carried via a separate set of optical pathways again situated inside the telescope. A video camera attached to the eye piece of the telescope forms a clear endoscopic image of the cavity on a TV monitor. The endoscopic surgeon has to continuously look at the TV monitor all through the endoscopic procedure.

Basic Layout of a ‘Continuous Flow Irrigation System:

Henceforth in this manuscript unless otherwise specified the term ‘distension’ shall be deemed to imply tissue cavity distension by ‘continuous flow irrigation’ only and the term ‘cavity’ unless specifically stated shall be deemed to refer to a ‘body tissue cavity’. In a typical distension system a physiological non viscous liquid like 0.9% normal saline, 1.5% glycine, mannitol, ringer's lactate and 5% dextrose is stored in a sterile fluid source reservoir. A fluid supply tube connects the said fluid reservoir with the inlet end of a pump. The outlet end of the inflow pump is connected to the inflow port of an endoscope. When the inflow pump operates the fluid from the fluid source reservoir is sucked via the fluid supply tube and the inflow pump pushes this fluid into the tissue cavity via the said inflow tube. The pump operates by consuming certain amount of energy and as a result of this a positive fluid pressure is created inside the tissue cavity. An outflow tube extends between the outflow port and the inlet end of an outflow pump. When the outflow pump operates it actively extracts waste fluid from the cavity again at the expense of energy and this waste fluid is ultimately sent to a waste fluid reservoir via a tube which connects the outlet end of the outflow pump with the waste fluid reservoir. Alternatively the outflow pump may be missing and in such case the outflow tube directly carries the waste fluid from the cavity to the waste fluid reservoir and the energy for such act is supplied by gravity instead of the outflow pump. Also, the inflow pump may be missing and in such case the inflow tube directly supplies the irrigation fluid from a fluid source reservoir to the cavity. In such case the fluid source reservoir is hung at a suitable height above the patient and the said energy for cavity distension is derived from gravity instead of the inflow pump. A suitable pressure transducer is attached to the inflow tube, the outflow tube or directly to the cavity to measure the fluid pressure. A controller may be incorporated to regulate the system.

The Simplest Continuous Flow Irrigation System:

In its simplest form, a continuous flow irrigation system comprises a fluid reservoir bottle hung at a suitable height above the patient and an inflow tube connecting this fluid reservoir to a tissue cavity. An out flow tube is incorporated to remove fluid from the tissue cavity. In this system there is no pump and no transducer. In such a system fluid flows from the fluid source reservoir into the cavity and the required energy is supplied by gravity. The pressure developed inside the cavity can be increased or decreased by elevating or lowering the height of the fluid source reservoir. In such system the main limiting factor is the height of the room ceiling beyond which the fluid reservoir cannot be raised. This is a crude system having negligible practical importance and has been included only from the academic point of view. Also in such a system unlimited volume of irrigation fluid may enter into the patient's blood circulation. Thus such system is not suitable even from the patient safety point of view.

Basic Components of a Continuous Flow Irrigation System:

Like a motor car is made up of certain obvious components like engine, tyres and a steering wheel, a continuous flow distending system is made of components like pump, pressure transducer, flow regulating valve, rubber tubes and a controller. The pump may be a positive displacement pump like a peristaltic pump, piston pump or a gear pump or alternatively it may be a dynamic pump like a centrifugal pump. Further the said pump may be of a fixed RPM type which runs at fixed RPM all through the endoscopic procedure or the pump may be of a variable RPM type which operates at variable RPM during the endoscopic procedure. It is extremely important to note that fixed RPM pumps and variable RPM pumps are two separate mechanical entities in context with a cavity distending system because the fixed and variable RPM pumps impart different surgical efficiency and patient safety criteria to the distending system. The said pump may be attached on the inflow side only, on the outflow side only or both on the inflow and outflow side. Further if a pump is attached only on the inflow side the outflow tube may directly empty in a waste fluid reservoir at atmospheric pressure or a vacuum source may also be additionally attached. In some distending systems a flow controlling valve is attached on the outflow tube in order to regulate the cavity pressure. There may be a single pressure transducer attached to the inflow tube, the outflow tube or directly to the cavity. In some systems instead of one pressure transducer two pressure transducers may be used, one on the inflow tube and the other on the outflow tube.

Relvant references have been included in a PCT application filed by the Inventors in the past numbered PCT/IB/002341 and the same may also be deemed to have been included in the present application. In addition, three references U.S. Pat. Nos. 5,520,638, 4,902,277 and 5,578,012 are now being included and discussed herebelow.

In the U.S. Pat. No. 5,520,638 a variable speed peristaltic pump is used to push irrigation fluid into a tissue cavity. This patent is related to the ‘Continuous Wave II Arthroscopy Pump’ marketed by Arthrex. A chamber with volume is connected to the inflow tube and a collapsible bladder is contained within the bladder. The collapsible bladder has an open end connected with tubing to a pressure transducer. Once activated the pump begins to introduce fluid into the tissue cavity via the inflow tube and as pressure builds within the tissue cavity, fluid enters the chamber, and air in the chamber is compressed. The compressed air in the chamber compresses the bladder. Air pressure in the bladder is experienced by the pressure transducer. The pressure transducer feeds pressure information to a controller which regulates the RPM of the pump on the basis of a pressure feedback mechanism. Thus by the help of a pressure feedback mechanism the pressure inside a tissue cavity is maintained by fluctuating around a desired value. In this invention an important purpose of the said chamber is to dampen the pressure pulsations created by the peristaltic pump. Such pressure pulsations create turbulence inside the tissues cavity and are hence undesirable. The method of dampening the pressure pulsations as described in this U.S. Pat. No. 5,520,638 is not adequately efficient, especially at high pump RPM's. The Inventors would like to submit that the system being claimed in the aforesaid US Patent is a passive dampening system. The system is only able to passively correct the small pressure pulsations. In the present invention a method shall be described by which the amplitude of the said pressure pulsations would be reduced to negligible magnitude even at a high pump RPM.

In U.S. Pat. No. 4,902,277 a pump is provided on the inflow side which pushes fluid into a tissue cavity while a positive displacement pump removes fluid from the cavity. This patent is related to ‘FMS duo Fluid Management System’ marketed by FMS Group. By the help of a pressure feedback mechanism the inflow pump is constantly increased or decreased thereby maintaining the cavity around a desired value. Thus by the help of a pressure feedback mechanism the pressure inside a tissue cavity is maintained by fluctuating around a desired value.

In U.S. Pat. No. 5,578,012 a centrifugal pump is deployed on the inflow side while no pump is deployed over the outflow side. This patent is related to the ‘HydroFlex HD’ pump marketed by DAVOL company. By the help of a pressure feedback mechanism the inflow pump is constantly increased or decreased thereby maintaining the cavity around a desired value. Thus by the help of a pressure feedback mechanism the pressure inside a tissue cavity is maintained by fluctuating around a desired value.

OBJECTS OF THE INVENTION

The overall objective of the invention is to provide a safe, efficient and turbulence free system for distending body tissue cavities for those endoscopic procedures which utilize continuous flow irrigation.

The main object of the invention is to minimize the amplitude as well as the frequency of pressure pulsations, inside the tissue cavity, created by the two positive displacement pumps.

Another object of the present invention is to provide a system for distending tissue cavities using which it being possible to create and maintain a desired precise cavity pressure for a desired precise rate at which fluid may be allowed to flow through the cavity, for any length of time.

Still another object of the present invention is to provide a system for distending tissue cavities using which it being possible to achieve a predictably constant clear endoscopic vision throughout the endoscopic procedure.

Yet another object of the present invention is to provide a system for distending tissue cavities using which it being possible to achieve predictably stable mechanical cavity distension throughout the endoscopic procedure.

One more object of the present invention is to provide a system for distending tissue cavities using which it being possible to predictably maintain the cavity pressure at any desired precise value despite physiological contractions of the cavity wall.

One another object of the present invention is to provide a system for distending tissue cavities using which it being possible to constantly, accurately and reliably determine the instantaneous real time rate of fluid intravasation into the patient's body by using two fluid flow rate sensors which do not have any movable components.

A further more object of the present invention is to provide a system for distending tissue cavities using which it being possible to maintain any desired precise and high cavity pressure without increasing the ‘maximum possible fluid intravasation rate’.

Another object of the present invention is to provide a system for distending tissue cavities using which it being possible to measure the actual cavity pressure, in an accurate, reliable and simple manner, by using a pressure transducer located far away from the cavity in the up stream portion of the inflow tube.

Yet another object of the present invention is to provide a system for distending tissue cavities using which it being possible to make the pressure inside the body cavity and the flow rate of the fluid passing through the body cavity absolutely independent of each other such that the value of any may be altered without affecting the value of the other.

Still another object of the present invention is to provide a system for distending tissue cavities using which it being possible to reduce the cavity filling time in a predictably controlled manner and at the same time achieving a desired cavity pressure at the end of the cavity refilling phase, cavity refilling time being the time taken to completely fill a cavity with the irrigation fluid.

One more object of the present invention is to provide a system for distending tissue cavities using which it being possible for the surgeon to have a fairly accurate assessment of the total volume of the irrigation fluid which would be required to complete the entire endoscopic procedure.

One another object of the present invention is to provide a system for distending tissue cavities using which it being possible for the surgeon to accurately know the maximum pressure which develop inside the cavity in case of an accidental obstruction of the outflow tube and it should be possible to minimize such rise in the cavity pressure in a controlled and predictable manner.

A further object of the present invention is to provide a system for distending tissue cavities using which it being possible to easily, quickly and safely change from one type of irrigation fluid to a different type of irrigation fluid, for example between normal saline and glycine, intraoperatively (that is during a surgical procedure), in any desired short period of time such that the cavity pressure does not change during such maneuver.

SUMMARY OF THE INVENTION

The present invention provides a safe and an efficient system for distending body tissue cavities for those endoscopic procedures which utilize continuous flow irrigation. The main aim of the invention is to minimize cavity fluid turbulence by minimizing the amplitude as well as the frequency of the pressure pulsations created by two positive displacement pumps. The present invention is a system of creating and maintaining a desired positive pressure inside a body tissue cavity through which fluid is made to flow at a desired flow rate. Alternatively the present invention may be considered as a system of creating cavity fluid pressure which is absolutely independent of the cavity outflow rate. The present invention comprises of two peristaltic pumps which work simultaneously, for indefinite time, at fixed flow rates to create and maintain any precise desired cavity pressure for any desired cavity outflow rate, including a zero outflow rate. One pump is located on the inflow side of a cavity while the other pump is attached to the out flow side of the cavity. Further if any fluid is being absorbed into or through the cavity walls, such as fluid intravasation which occurs during hysteroscopic endometrial resection, the instantaneous real time rate of such fluid absorption can be constantly determined. Also the cavity pressure can be maintained at any desired high value without increasing the ‘maximum possible fluid intravasation rate’. In the proposed invention by incorporating a system of pump synchronization it is possible to reduce fluid turbulence to almost negligible levels. The proposed invention also has multiple other features of endoscopic surgical relevance which greatly enhance the patient safety and efficiency during endoscopic surgery few such features being shortening of the cavity refilling time in a predictably controlled fashion, to be able to predict by a fair degree of accuracy the volume of fluid which would be required to complete the endoscopic procedure, to be able to quickly switch during endoscopic surgery between two types of irrigation fluids without varying the cavity pressure and to be able to predict and limit the magnitude of the maximum increase in the cavity pressure or the magnitude of a minor pressure surge which might occur in case of an accidental obstruction of the outflow tube for a specific outflow rate. Also the same system can be used for all types of endoscopic procedures which utilize continuous flow irrigation.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows the main block diagram of the invention along with the ‘pressure pulse dampening system’ and the controller.

FIG. 2 shows the block diagram of the invention without the ‘pressure pulse dampening system’.

FIG. 3 is similar to FIG. 2 except that the controller has not been included.

FIG. 4 shows the inflow part of the system along with the inflow peristaltic pump 5, the pressure transducer 17 and the constriction site 8.

FIG. 5 is similar to FIG. 3 except that in this figure a shaded region represents an area having an almost similar pressure.

FIG. 6 is similar to FIG. 3 except that an optional constriction housing tube 17 and an optional pressure transducer 63 have been included.

FIG. 7 shows is the schematic diagram for pump synchronization on a common rotor shaft.

FIG. 8 shows the basic lay out of the ‘pressure pulse dampening system’.

FIG. 9 shows a detailed layout of the syringe mechanism along with a coupling means.

DETAILED DESCRIPTION OF INVENTION

Accordingly, the present invention provides a system for distending body tissue cavities of subjects by continuous flow irrigation during endoscopic procedures the said system comprising:

-   a fluid source reservoir containing a non viscous physiologic fluid     meant for cavity distension; -   a fluid supply conduit tube connecting the fluid source reservoir to     an inlet end of a variable speed positive displacement inflow pump     and an outlet end of the said inflow pump being connectable to an     inflow port of an endoscope instrument through an inflow tube for     pumping the fluid at a controlled flow rate into the cavity, the     flow rate at which the fluid enters into the cavity via the inflow     tube being termed as the cavity inflow rate; -   an inflow pressure transducer being located anywhere in the inflow     tube between the outlet end of the inflow pump and the inflow port     of the endoscope; -   an inflow pressure pulsation dampening means connected to the inflow     tube for dampening the pressure pulsations inside the cavity created     by the positive displacement inflow pump, -   an outflow port of the endoscope being connectable to an inlet end     of a variable speed positive displacement outflow pump through an     outflow tube for removing the fluid from the cavity at a controlled     flow rate, the flow rate of the said outflow pump being termed as     the cavity outflow rate, -   an outflow pressure pulsation dampening means connected to the     outflow tube for dampening the pressure pulsations inside the cavity     created by the positive displacement outflow pump; -   an outlet end of the outflow pump being connected to a waste fluid     collecting container, and -   a housing tube having a controllable constriction site is being     provided between the fluid source reservoir and the inflow tube such     that the same by-passes the inflow pump; wherein housing tube     provides a route for any excess fluid being pumped by the inflow     pump to bypass the inflow pump and go back to the fluid supply tube     or the fluid source reservoir, thereby minimizing turbulence inside     the cavity and maintaining the cavity pressure at a stable value     despite physiological contractions of the cavity wall.

In an embodiment of the present invention, the fluid source reservoir containing the non-viscous physiologic fluid is maintained at atmospheric pressure or at a pressure greater than the atmospheric pressure.

In another embodiment of the present invention, a proximal open end of the fluid supply tube is connected to the fluid source reservoir and a distal end of the tube is connected to the inlet end of the variable speed positive displacement inflow pump.

In yet another embodiment of the present invention, the proximal open end of the fluid supply tube is constantly and completely immersed in the fluid source reservoir.

In still another embodiment of the present invention, a proximal end of the inflow tube is connected to the outlet end of the variable speed positive displacement inflow pump and a distal end of the inflow tube being connectable to the inflow port of the endoscope instrument.

In a further embodiment of the present invention, the variable speed positive displacement inflow pump is selected from the group comprising peristaltic pump, piston pump, gear pump, diaphragm pump and plunger pump.

In one more embodiment of the present invention, the variable speed positive displacement inflow pump is a peristaltic pump.

In one another embodiment of the present invention, the housing tube is releasably provided between the fluid source reservoir and the inflow tube to enable replacement of the housing tube with yet another housing tube having a different diameter at the constriction site to suit the operational need of the endoscopic procedure.

In one further embodiment of the present invention, a proximal end of the housing tube is connected to the fluid supply tube near its distal end close to the inlet port of the inflow pump.

In a further more embodiment of the present invention, a proximal end of the housing tube empties directly into the fluid source reservoir and is constantly and completely immersed in the fluid source reservoir.

In an embodiment of the present invention, a distal end of the housing tube is connected to the inflow tube near its proximal end close to the outlet end of the inflow pump.

In another embodiment of the present invention, the housing tube is provided with a clamping means at the constriction site to enable the user to vary the diameter of the housing tube at the constriction site to suit the operational needs of endoscopic procedures.

In yet another embodiment of the present invention, the diameter of the housing tube at the constriction site is in the range of 0.001 mm to a maximum value which is less than the overall diameter of the rest of the housing tube.

In still another embodiment of the present invention, the diameter of the housing tube at the constriction site is in the range of 0.01 to 2.5 mm.

In one more embodiment of the present invention, the inflow pressure transducer is located sufficiently away from the cavity site, preferably near the outlet end of the inflow pump from the practical point of view, such that the fluid pressure measured by the same is almost equal to the fluid pressure inside the cavity.

In a further embodiment of the present invention, a proximal end of the outflow tube being connectable to the outlet port of the endoscope instrument and a distal end of the outflow tube is connected to an inlet end of the variable speed positive displacement outflow pump.

In one another embodiment, the present invention further comprising an outflow pressure transducer connected between the proximal end of the outflow tube and the inlet end of the variable speed positive displacement outflow pump for measuring the pressure in the outflow tube.

In one further embodiment of the present invention, the variable speed positive displacement outflow pump is selected from the group comprising peristaltic pump, piston pump, gear pump, diaphragm pump and plunger pump.

In an embodiment of the present invention, the variable speed positive displacement outflow pump is a peristaltic pump.

In another embodiment of the present invention, the outlet end of the variable speed positive displacement outflow pump is connected to the waste fluid collecting container through a waste fluid carrying tube.

In yet another embodiment, the device of the present invention further comprising a micro-controller means electrically coupled to the inflow pressure transducer, the outflow pressure transducer, the inflow pump and the outflow pump for regulating the operation of the inflow and the outflow pumps.

In still another embodiment, the device of the present invention further comprising a housing tube having a variable size constriction site being provided between the outflow tube and the waste fluid reservoir.

In a further embodiment of the present invention, the distal end of the housing tube is connected to the waste fluid carrying tube.

In one more embodiment of the present invention, the fluid supply tube, the inflow tube, the outflow tube and the waste fluid carrying tube are flexible, disposable and are made of polymeric material.

In one another embodiment of the present invention, the inflow and the outflow positive displacement pumps are coupled to a common shaft for synchronously operating these two pumps.

In one further embodiment of the present invention, the inflow housing tube is provided with an electromechanical device, a solenoid, to enable the micro-controller to vary the diameter of the constriction site.

In an embodiment of the present invention, wherein if the inflow and the outflow pumps are coupled to the common shaft, the inflow housing tube is essentially provided with the micro-controller controlled solenoid for varying the diameter of the constriction site.

In another embodiment of the present invention, the variable speed inflow and outflow peristaltic pumps are provided with 1 to 5 peristaltic pump tubes connected in parallel between the inflow and outflow ends of the peristaltic pumps for reducing the frequency of pulsations in the pressure, the said tubes being connected to each other at the inflow and outflow ends of the peristaltic pumps, and the said peristaltic pump tubes being the ones which come in contact with the rollers of the peristaltic pumps.

In yet another embodiment of the present invention, the inflow pressure pulsation dampening means comprises a single outlet syringe mechanism, the piston of the same being coupled synchronously to the positive displacement inflow pump through a coupling means and a single outlet end of the said syringe mechanism being connected to the inflow tube.

In still another embodiment of the present invention, the outflow pressure variation dampening means comprises a single outlet syringe mechanism, the piston of the same being coupled synchronously to the positive displacement inflow pump through a coupling means and a single outlet end of the said syringe mechanism being connected to the outflow tube.

In one more embodiment of the present invention, if the inflow and the outflow pumps are operated synchronously by coupling them to the common shaft, the inflow and/or the outflow pressure variation dampening means are optionally operated synchronously by coupling them to the same common shaft.

In one another embodiment of the present invention, a fluid flow rate sensor is located in the lumen or wall of the fluid inflow tube for measuring the cavity inflow rate.

In yet another embodiment of the present invention, the fluid flow rate sensor is located between the inflow port of the endoscope and the location where the housing tube is connected to the fluid inflow tube.

In still another embodiment, the device of the present invention further comprises a fluid flow rate sensor connected between the proximal end of the outflow tube and the inlet port of the variable speed positive displacement outflow pump for measuring the cavity outflow rate.

In one more embodiment of the present invention, the fluid flow rate sensor is located between the outflow port of the endoscope and a place proximal to the point where the said additional/optional housing tube is connected to the outflow tube.

In one another embodiment of the present invention, the fluid flow rate sensors consists of a heating coil in physical contact with a metal plate for heating the same and a temperature sensor placed in contact with the metal plate for measuring the temperature of the said metal plate, the temperature of the metal plate being a function of the fluid flow rate.

In a further embodiment of the present invention, the fluid flow rate sensor is a hot wire anemometer.

In a further embodiment of the present invention, instantaneous real time rate of fluid intravasation is determined by electrically connecting the inflow and outflow fluid flow rate sensors to a micro-controller.

In a further more embodiment of the present invention, the fluid source reservoir, the inflow pump, the tubes, the tissue cavity, and the out flow pump are placed approximately at the same height with respect to a horizontal ground.

In another embodiment of the invention the two positive displacement pumps, which may be peristaltic pumps, are attached on a common single central shaft such that a single motor operates both pumps simultaneously and such arrangement being provided as it further reduces fluid turbulence inside the tissue cavity.

The proposed invention is described hereafter with reference to the accompanying drawings in order to clearly explain and illustrate the system and the working of the system. It is respectfully submitted the scope of the invention should not be limited by the description being provided hereafter.

The system of the present invention is a unique system for distending body tissue cavities in endoscopic procedures. In the proposed invention a body tissue cavity is distended by continuous flow irrigation in such a manner that the amplitude of the pressure pulsations created by the positive displacement pumps can be reduced to a negligible value. In the proposed invention a method of reducing of the said pulsations has been described. Also the cavity pressure is absolutely independent of the cavity outflow rate, such the both, the cavity pressure and the outflow rate, may be independently altered without varying the value of the other parameter.

FIG. 1 shows the main diagram of the invention. In FIG. 1 the inflow and the outflow ‘pressure pulse dampening systems’, have been shown clearly. However in order understand the invention in a simpler manner, first the basic invention without the ‘pressure pulse dampening systems’ shall be discussed. The basic schematic diagram of the invention is shown in FIG. 2. FIG. 2 is similar to FIG. 1 except that in FIG. 2 the two ‘pressure pulse dampening systems’ have not been included. The two peristaltic pumps 5 and 14 operate simultaneously in order to distend a tissue cavity in such a manner that the cavity pressure is totally independent of the cavity outflow rate. FIG. 2 represents the complete basic schematic diagram of the invention. Please note that the controller being used in the system shown in FIG. 2 is an optional feature and the system would provide most of the features even without the controller. The FIG. 3 represents the schematic diagram of the invention but without a controller system. Thus FIG. 3 is a basic mechanical version of the invention. A human operator is required to operate such mechanical version of the invention shown in FIG. 3. Though it is recommended that the controller based version of the invention be used in endoscopic surgeries, it is not essential. The controller being used in the present invention merely assists the user in arriving easily at some of the additional functions which otherwise can be performed manually. Thus, in this manuscript the mechanical version of the invention shown in FIG. 3 is being discussed in more detail in order to explain the basic physical principals of the invention with a greater clarity.

Referring to FIG. 3, the system shown in this figure comprises of two peristaltic pumps which can maintain a predictably precise stable cavity pressure for indefinite time by working simultaneously at constant rotational speeds. Pump 5 pushes fluid into the cavity 18 and while pump 14 simultaneously extracts fluid out of the cavity 18. The inlet end of the inflow peristaltic pump 5 is connected to a fluid source reservoir 1 via tube 2. The distal open end of tube 2 is constantly submerged in a sterile non viscous physiological fluid like 0.9% normal saline, 1.5% glycine, ringer lactate or 5% dextrose contained inside the reservoir 1 at atmospheric pressure. One end of the tube 7 connects the ‘T junction’ 3 situated at the inlet end of the pump 5 while the other end of tube 7 connects with the ‘square junction’ 6 situated at the outlet end of the pump 5. The ‘T’ junction 3 is thus the meeting point of three tubes, namely 2, 4 and 7. Similarly the square junction 6 is the meeting point of four tubes, 4, 9, 7 and 10. The rollers of the peristaltic pump 5 continuously compress and roll over the entire length of tube 4 thus displacing fluid in the direction of the curved arrow. This curved arrow denotes the direction in which the rollers of the peristaltic pump 5 rotate. Tube 7 has a constriction point 8 which can be located anywhere along its length. Such constriction point refers to a point where the inner diameter of the lumen of tube 7 is reduced in comparison to the lumen of the rest of the tube 7. Such constriction may be a permanent constriction in the lumen of tube 7 or it may be a variable constriction whose diameter may be increased or decreased as desired. A pressure transducer 17 is attached at one of tube 9 while the other end of tube 9 is connected anywhere on inflow tube 10. For practical convenience it is desirable that the said other end of tube 9 be connected in the up stream part of the inflow tube 10 such as at the square junction 6. The pressure transducer 17 measures the fluid pressure via a column of liquid or air present in the lumen of tube 9. The fluid pressure as measured by the pressure transducer shall be referred to as P. In this manuscript the term ‘P’ shall frequently be used to refer to the actual pressure inside the tissue cavity but in physical terms P is the pressure sensed by the transducer 17 at point 6. The pressure transducer 17 may also be in the form of a membrane diaphragm incorporated in the wall of the inflow tube 10 such that this membrane diaphragm is in direct contact with the fluid contained in the inflow tube 10, such that the linear movement excursions of the said membrane are, interpreted as pressure of the fluid inside the inflow tube 10 by a suitable pressure transducer. Such type of pressure sensor being directly incorporated in the wall of the inflow tube 10 senses the fluid pressure without the intervention of tube 9. The basic purpose of the transducer is to measure the fluid pressure inside the inflow tube 10, such as at point 6, thus the mechanical construction of the transducer is not important as long as it measures the fluid pressure. For the sake of simplicity the existence of tube 9 shall be continued to be considered in the rest of the manuscript. The peristaltic pump 14 attached to the outflow side actively extracts fluid out of the tissue cavity 18 via the out flow tube 12. The outlet end of the pump 14 is connected to a waste fluid carrying tube 15 which opens into a waste fluid collecting reservoir 16 at atmospheric pressure. The rollers of the pump 14 constantly compress and roll over the entire length of the peristaltic pump tubing 13 thus displacing fluid in the direction of the curved arrow which also corresponds with the direction of pump rotation.

In order to understand the invention in a simpler manner both pumps are being considered to be identical in all respects and all the tubes, the inflow and out flow port are also being considered to be having the same uniform inner diameter. However the inner diameter of the tubes and the inflow and outflow ports can also be different. The inflow and outflow ports are metallic adaptors located at the proximal end of the endoscope and are meant to connect with the inflow and outflow tubes respectively, however the said inflow and outflow ports have not been separately shown in any of the figures. Tubes 4 and 13 consist of a soft resilient plastic material which can be efficiently compressed by the rollers of the peristaltic pumps. The other tubes also consist of a suitable resilient plastic material. It is assumed that all the components shown in FIG. 3, including the two pumps, all tubes and the said cavity, are placed at the same horizontal height with respect to the ground. Also the rollers of pumps 5 and 14 should press adequately over tubes 4 and 13 in such a manner that there is no leak through these tubes when the pumps are stationary. It is also assumed that there is no abnormal leak of fluid in the irrigation system, for example leak via a accidental hole made in any irrigation tube or a fluid leak which might occur if the endoscope loosely enters into the tissue cavity, for example in hysteroscopic surgery fluid leaks by the sides of the endoscope if the cervix is over dilated.

One end of the constriction site housing tube 7 instead of being connected with tube 2 at the ‘T’ junction 3 can also open directly into the fluid source reservoir 1. This shall not affect the efficiency of the system in any way but it may be practically difficult from the surgical point of view in some special cases. Thus such a provision is separately shown in FIG. 6 and the said tube has been labeled as 11 but it has intentionally not been included in FIGS. 1,2 and 3 in order to keep the drawings simple. Also a constriction site housing tube similar to tube 7 labeled as 117 can be attached to the outflow tube 12 as shown in FIG. 6. In the said tube 117 the said constriction site is labeled as 119. Such tube can serve a number of purposes. Tube 117 can be utilized for relatively faster evacuation of air bubbles from the cavity. The said bubbles are invariably created inside the cavity as a result of electrosurgical cutting and coagulation or they may enter the cavity while the endoscope is being introduced into the cavity. Such bubbles cause extreme nuisance for the surgeon because they obscure vision and thus the surgical time may be greatly increased. In routine surgery the surgeon moves the tip of the resectoscope near the bubble and the bubble is sucked out of the cavity by the process of continuous flow irrigation. However in certain situations it may not be possible to bring the tip of the resectoscope near the bubble, one such situation is when bubbles accumulate inside a very deep cornuae associated with a long septum, the diameter of the cornuae being less than the outer diameter of the resectoscope. In such a situation the tubal opening situated at the center of the cornuae can only be visualized after evacuating such bubbles from the cavity. In such situation the bubbles can be quickly evacuated without moving the tip of the resectoscope near the bubbles by simply opening the constriction 119 in the tube 117. However such maneuver tends to completely collapse the cavity. Thus if the resctoscope tip is only moderately away from the bubbles the constriction is opened only partially so that the bubbles are sucked out and the cavity collapses by a relatively smaller magnitude. In place of the adjustable constriction site 119 a pressure release safety valve may be incorporated as a safety feature, however it is more beneficial to install such pressure safety valve in the inflow circuit. The tube 117 may also be used for quickly flushing air bubbles from the irrigation tubes by fully opening the constriction site 119 for a few minutes or seconds. The tube 117 may also be used for any other purpose as deemed fit by the surgeon. However the said tube 117 has intentionally not been included in the main block diagrams of the invention because by including the tube 117 in the main block diagrams it would have become very difficult to explain the basic physical principals of the invention. However tube 117 is a very beneficial component and is thus recommended to be incorporated in the system of the proposed invention. The opening and closing of the constriction site 119 can also be regulated manually to help in various special advanced endoscopic applications. Incorporation of tube 117 with the variable constriction site 119 can help in reducing the substantially high amplitude pressure variations inside the cavity caused by abnormally large cavity wall contractions, but such phenomenon is only rarely encountered. Also an additional pressure transducer 63 may also be attached on the out flow tube 12, if desired, as shown in FIG. 6. However the said pressure transducer 63 has intentionally not been included in the main block diagrams of the invention because by doing so it would have become very difficult to explain the basic physical principals of the invention.

In order to clearly understand the system shown in FIG. 3 it would be helpful to discuss the functioning of the inflow peristaltic pump 5 as a separate entity as shown in FIG. 4. The rollers of pump 5 move in the direction of the curved arrow and squeeze over the entire length of peristaltic pump tubing 4. Initially tubes 2, 4, 7 and 9 contain air at atmospheric pressure and the free open end of tube 2 is submerged in a sterile fluid contained inside the fluid source reservoir 1. The moment the constriction site 8 is fully occluded a column of fluid is immediately sucked into tube 4 via tube 2, and thus fluid starts accumulating in the proximal parts of tubes 9 and 7. As the fluid fills in tube 9 it pushes a column of air distal to the fluid column created in tube 9 and the pressure of this compressed air column is sensed by the pressure transducer 17. The fluid pressure and the pressure of the said compressed air column are same thus the pressure transducer 17 actually senses the fluid pressure. If tube 7 continues to remain fully occluded at the constriction site 8, the fluid continues to accumulate inside tubes 9 and in that part of tube 7 which lies between point 6 and the constriction site 8, and the pressure transducer 17 thus displays a continuously rising fluid pressure. The moment the block at the constriction site 8 is partially released the fluid escapes in the form of a jet through the partially open constriction opening 8 in the direction of point 3. With the constriction opening 8 being only partially blocked, if the pump 5 continues to rotate at a constant rotational speed the fluid pressure ultimately gets stabilized at a fixed value provided the internal diameter of the constriction site 8 is not further varied. The diameter D of the constriction site 8 ranges from a minimum non-zero value to a maximum value which is less than the overall diameter of the rest of the housing tube, that is range between when the constriction site 8 is fully occluded, to a maximum value which is less than the diameter of tube 7. Henceforth in this manuscript the inner diameter of the constriction site 8 shall be deemed to be fixed at some predetermined value D, unless otherwise stated.

Referring to FIG. 5, this figure is similar to FIG. 3 but a limited region of the irrigation circuit having an almost same pressure has been shaded black. Due to frictional resistance experienced by the moving fluid the pressure at point 6, as sensed by the transducer 17, is always found to be higher than the actual pressure inside the tissue cavity 18 but the said pressure difference is so small that it may be neglected from the practical surgical point of view. Also such pressure difference increases as the fluid flow rate increases. In a simulated experimental endoscopic model, as explained hereafter, such pressure difference was found to be only 2 mm Hg at a out flow rate of 500 ml/minute, while at outflow rates less than 400 ml/minute this pressure difference was so small that it had not been possible to demonstrate it experimentally. The term ‘out flow rate’ being referred to the flow rate of pump 14. Also, the said pressure difference remains constant all through surgery at any fixed outflow rate. Though the said pressure difference is negligible but if desired its effect can also be totally negated by subtracting its value from the pressure reading of the transducer. In this manner, in endoscopic surgeries, it is possible to determine the actual cavity pressure by using the pressure transducer 17 located far away from the cavity. This feature is of special relevance because in endoscopic procedures like hysteroscopy, arthroscopy and brain endoscopic surgery while it is important to know the actual cavity pressure but at the same time it is practically difficult to take a pressure measurement directly from the cavity.

Referring to FIG. 3 it shall be first described as to how the system of the proposed invention can be used mechanically, that is without a controller. The peristaltic pumps 5 and 14 can be made to work at any fixed rotational speed and the fluid flow rate of each pump is directly proportional to the pump RPM or the pump rotational speed. Thus any precise pump flow rate can be generated by selecting a suitable pump rotational speed. The fluid flow rate of pump 14 shall henceforth be denoted by R2 and shall be termed as the ‘outflow rate’. The fluid flow rate of pump 5 shall be denoted by R1 and shall be termed as the ‘inflow rate’ Here it is to be noted that the term ‘inflow rate’ R1 is not the true inflow rate for the cavity 18, as might be suggested by the literary meaning of the term ‘inflow’ because R1 is not the actual rate at which fluid into the cavity 18 because some fluid also constantly escapes through the constriction site opening 8. Henceforth in the entire manuscript the term ‘inflow rate’ shall only be referred to the flow rate of the inflow pump 5 unless specifically mentioned. However the term ‘outflow rate’ R2 does correspond to the literary meaning of the term ‘outflow’ because R2 is equal to the rate at which fluid flows out of the cavity 18. The surgeon initially decides an out flow rate R2 by selecting a suitable rotational speed for pump 14. Next the surgeon decides the maximum flow rate at which fluid could be allowed to enter into the cavity via the inflow tube 10 and the inflow pump 5 is set to work at such flow rate or at a flow rate slightly lesser than this. As already discussed, intravasation is process by which fluid enters into the patient's blood circulation through the cut ends of blood vessels located in the cavity wall or enters into the patient's body, for example into the peritoneal cavity, as a result of an accidental perforation or escapes via patent fallopian tubes into the peritoneal cavity. Thus ‘intravasation’ is a process by which the pressurized irrigation fluid enters into the patient's body system through the walls of the tissue cavity. In case of a surgical accident like cavity wall perforation the fluid being pumped by the inflow pump 5 can enter into the patient's body at a rate almost equal to R1. It is obvious that the maximum rate of fluid intravasation cannot exceed the value R1. In case of an accident like cavity wall perforation it may take some time before an abnormally high intravasation rate is discovered and in such time a dangerous quantity of fluid might enter into the patient's body. If the inflow rate R1 is kept at a relatively lower value then the volume of intravasated fluid in case of such an accident would be low. After fixing the values for R2 and R1 the system is started and the diameter of the constriction site 8 is gradually reduced. As the diameter of the constriction site 8 is reduced fluid starts flowing into the tissue cavity and the pressure inside the tissue cavity starts rising. When the desired pressure is achieved inside the tissue cavity the diameter of the constriction site 8 is not reduced any further and is fixed. The diameter of the constrictions site at this stage is termed as “D”. The constriction site may also be a plastic or metal piece which has a hole in the centre such that the diameter of the hole is permanently fixed at some value D. If a constriction 8 has a permanently fixed diameter then only the flow rates of pumps 14 and 5 have to be set before the system becomes completely operational.

The Inventors here would like to discuss about the importance of incorporating the housing tube 7 with the constriction site and the non-obvious advantages provided by the housing tube 7 with the constriction site.

As mentioned earlier, till date the surgeons were left with only two options, either to ignore the said cavity pressure variations by not correcting them, or to externally and actively correct such pressure variations. To externally and actively correct the variations in the cavity pressure, controller was incorporated and the working of the pumps were essentially controlled by the controller. Incorporation of the controller controlling the operation of the pumps did not provide any benefit. The controllers used to activate the controlling action after the variations in the cavity pressure had subdued. Thus, the controlling action initiated by the controller instead of benefiting the surgeon leads to an undesirable turbulence inside the cavity and also tends to amplify the resultant movement excursions of the cavity walls.

The Inventors have noticed that if the controller continuously controls the operations of the pumps (either on the inflow side or on the outflow side), the cavity pressure continuously fluctuates around a preset value and it not at all possible to attain a constant value. The Inventors believe that the controller provides proper corrective action (by continuously controlling the operations of the pumps) only if the fluctuations in the cavity pressure are gradual and not highly instantaneous. That is, if the quantitative rise/fall in the cavity pressure is over long time period, the controller would be able to provide proper corrective action. As the time period to detect variation in the cavity pressure and commence corrective action is ideally in the range of 2 to 4 seconds, if the quantitative rise/fall in the cavity pressure is over very short time period, the suggested mechanism of providing a controller will be unsuitable. Under such instances, instead of providing any corrective action, the controller destabilizes the system and induces additional pressure fluctuations inside the cavity (because of commencing a corrective action at a delayed stage). Thus it takes very long time period for the system to once again get stabilized.

The Inventors have surprisingly found that by incorporating a housing tube provided with a constriction site at the inflow side as described above, inherently and passively corrects the pressure variations due to physiological cavity wall contractions and the mechanical movement of the tubes and the endoscope and also limits the variation in the size of the cavity. The Applicants would like to highlight that it is important to control both the variations in the pressure inside the cavity and the changes in the size of the distended cavity. Large variations in the pressure inside the cavity or the size of the cavity are detrimental to the surgical procedure. In all the prior art systems attempts were made to either control the variations in the pressure or the variations in the cavity size. But none of the prior art document the need to control both the cavity pressure variations and the cavity size variations and hence failed to provide a safe and ideal system. During the contraction of the cavity, a minute quantity of the fluid is pushed out of the cavity. If during this stage the system does not provide a way for releasing the fluid being pushed out, the instantaneous pressure inside the cavity increases tremendously which is harmful to the patient. On the other hand, if the amount of fluid being pushed out of the cavity is not checked and controlled, the changes in the size of the distended cavity are very high. The incorporation of the housing tube having the constriction site for the first time in the present system controls both the variations in the pressure inside the cavity and the changes in the size of the distended cavity. The housing tube having the constrictions site provides a by-pass route for the fluid being pushed out of the cavity to go back to the fluid supply tube or the fluid source reservoir. This avoids the instantaneous pressure surge inside the cavity which is harmful to the patient. The size of the diameter at the constriction automatically controls the amount of fluid passing through the housing tube, thereby controlling the amount of fluid being pushed out of the cavity. Inclusion of the housing tube with the constriction site therefore minimizes the instantaneous variations in the size of the distended cavity.

Alternatively if the cavity expands a suitable volume of fluid is sucked into the cavity from the irrigation circuit, such as from the region of point 6, and this is accompanied by a corresponding transient decrease in the flow rate at which fluid which fluid is escaping via the constriction site 8 in the direction of point 3 but if the magnitude of the said physiological expansion is more fluid may even be sucked into the cavity via the constriction site 8. This implies that the constriction site 8 is helping in maintaining a stable cavity pressure despite physiological cavity wall contractions by suitably varying the magnitude of an imaginary fluid flow vector passing through the constriction site 8.

Cavity Pressure or the Outflow Rate, Both can be Altered Independently Without Varying the Value of the Other Parameter:

Referring again to FIG. 3 an hypothetical endoscopic procedure is being considered where surgery is being performed at an outflow rate R2 and inflow rate R1 with the constriction 8 diameter being been fixed at some value D and a resultant cavity pressure P being created maintained. In such hypothetical situation as long as R2 and R1 are not altered the cavity pressure P remains predictably constant throughout surgery resulting in a predictably stable mechanical distension of the tissue cavity walls which culminates in constant clear visualization throughout the endoscopic procedure. If in the said hypothetical procedure the cavity pressure needs to be increased without altering the out flow rate R2 then all that is needed is to start increasing the value of R1 and stop doing so when the desired higher cavity pressure is achieved. Similarly if the cavity pressure needs to be decreased without altering the out flow rate R2 then R1 is decreased till the desired lower cavity pressure is attained. In the said hypothetical endoscopic procedure if the outflow rate R2 needs to be increased without altering the cavity pressure P then the value of R2 is increased by the desired magnitude but simultaneously the value of R1 is also increased by a similar magnitude. Similarly, if the outflow rate R2 needs to be decreased without altering the cavity pressure P then the value of R2 is decreased by the desired magnitude but simultaneously the value of R1 is also decreased by a similar magnitude. Thus if R1 and R2 are simultaneously increased or decreased by the same magnitude the cavity pressure does not vary, the value D is always fixed as already stated. The preceding statements shall now be explained by the help of a numerical hypothetical example. In reference to FIG. 3 considering a hypothetical situation in which an endoscopic procedure is being done at an outflow rate of 100 ml/minute, an inflow rate R1 and the cavity pressure being 80 mm Hg. If the surgeon wants to increase the outflow rate to 322 ml/minute by maintaining the cavity pressure at the same value of 80 mm Hg outflow rate is increased to 322 ml/minute and the inflow rate is increased by 222 ml/minute, because 322 ml/min−100 m/min=222 ml/minute. As already mentioned in this paragraph if both inflow and outflow rates are increased or decreased by the same magnitude the cavity pressure does not change. Thus the final inflow rate becomes R1+222 ml/minute, where R1 was the initial inflow rate. Thus in the proposed invention the cavity pressure and the outflow rate both can be altered absolutely independent of each other without affecting the value of the other parameter.

Mechanical Version of the Invention:

The mechanical version of the invention shown in FIG. 3 can be used practically in endoscopic surgeries but it requires a skilled operator having a detailed knowledge of the physical principals involved in cavity distension, which may not be always possible. Also the mechanical version has certain practical limitations which shall be explained in the later sections of the manuscript. This mechanical version of the invention has been discussed only in order to explain more clearly the physical principals associated with the controller based version of the basic invention shown in FIG. 2 and the main invention shown in FIG. 1.

Controller Based Version of the Invention:

Referring to FIG. 2, this figure shows a schematic diagram of the basic invention without the ‘pressure pulse dampening system’. FIG. 2 and FIG. 3 are similar except that in figure except that in FIG. 3 the controller system is not included. A tachometer, not shown in the diagrams, is coupled to each peristaltic pump and sends information regarding the pump rotation speed to the controller 19 via wires 60 and 58. The pump flow rates being proportional to the pump rotation speed the tachometer signal always conveys flow rate related information to the controller. As already mentioned in paragraph 51 both peristaltic pumps have been considered to be similar in all respects because this makes it easier to understand and operate the system. However the two peristaltic pumps may also be different in context with the inner diameter of the peristaltic pump tubes 4 and 13 but in such case suitable modifications have to be made in the controller programming in order to operate the system as described in this manuscript. The controller also regulates the rotation speed of the two pumps via electrical signals sent through wires 59 and 61. The pressure transducer 17 conveys the pressure signal to the controller via wires 62. On the basis of a pressure feed back signal received from the pressure transducer 17 the controller regulates the rotational speed of the inflow pump 5. The outflow pump 14 works at fixed outflow rates and the flow rate of this pump is also regulated by the controller via suitable electrical signals sent via wires 61. A provision exists by which desired values for P and R2 can be fed into the controller and the values R1, R2 and P can be continuously displayed via suitable display means incorporated in the controller. The controller can be programmed to perform many special functions related to endoscopic surgery.

Method of Operating the Controller Based Version of the Invention:

Again referring to FIG. 2, in context with the present invention at the start of surgery the surgeon initially selects suitable values for cavity pressure P and outflow rate R2. The said desired values of P and R2 are fed into the controller via suitable input means incorporated in the controller. The diameter D at the constriction site 8 remains fixed at some pre selected value. The diameter of the constriction site 8 is so chosen that it suits the operational needs of the endoscopic procedure. When the system shown in FIG. 2 is operated the controller 19 instructs the outflow pump 14 via wires 61 to continuously extract fluid out of the body cavity 18 at a desired fixed outflow rate R2. Thus all through the surgery the outflow rate remains fixed at R2 irrespective of any internal or external factors unless intentionally changed by the surgeon. The cavity pressure is sensed by the pressure transducer 17 and a corresponding pressure feedback signal is sent to the controller via wires 62 on the basis of which the controller regulates the inflow rate R1, via wires 59. After the system is made operational the controller 19 gradually increases the inflow rate up to the point where the desired preset cavity pressure P is achieved. Let the value of the inflow rate at which the desired cavity pressure is achieved be termed as ‘R1.Final’. It is obvious that the value ‘R1.final’ is actually determined by the controller by a pressure feed back mechanism and such determination of the value ‘R1.Final’ is based on the preset values of R2 and P. The controller is so programmed that once the value ‘R1.Final’ is achieved and is maintained for a desired minimum time interval, for example 10 seconds, after which the controller releases the inflow pump 4 from its pressure feedback control mechanism and allow the inflow pump 4 to operate on its own at an inflow rate ‘R1.Final’ which was determined by the controller. In this manner the two peristaltic pumps continue to work at fixed flow rates to maintain a desired stable cavity pressure. The controller is also programmed that in case the cavity pressure subsequently alters, for example due to intravasation, by a desired minimum preset magnitude and for a desired minimum time, which may hypothetically be 10 seconds, the inflow pump 4 again comes under the pressure feedback control of the controller and a new value of ‘R1.Final’ is determined by the controller after which the inflow pump 4 is again allowed to be operated without the pressure feedback mechanism at the newly determined ‘R1.Final’ inflow rate. Such sequence of events continue to occur throughout the endoscopic procedure. Taking an imaginary example if the total surgical time is 60 minutes then it may be hypothetically possible to operate the inflow pump independent of the pressure feedback mechanism for 55 minutes and under the control of the pressure feedback mechanism for 5 minutes. However, provision of operating the inflow pump 4 under a pressure feedback mechanism all through the endoscopic procedure can also be incorporated.

The Advantage of Operating the Inflow Pump Independent of the Pressure Feedback Mechanism:

The only reason for operating the inflow pump 4 independent of the pressure feedback mechanism is to avoid unnecessary corrections of minor pressure variations caused by physiological cavity wall contractions. The concept of physiological cavity wall contractions has been explained in detail under the heading ‘basic physics of cavity distension’. In the present invention the physiological variations in cavity pressure are automatically corrected by the constriction site 8 without the need of a controller. If the cavity contracts a minute quantity of fluid which is pushed out of the cavity escapes via the constriction site 8 towards point 3. It is to be noted that the part of tube 7 between point 8 and 3 is at atmospheric pressure thus the fluid which is expelled from the cavity as a result of a physiological contraction escapes through the constriction site 8 against a zero pressure head, which being atmospheric pressure. Thus, the transient, insignificant and instantaneous rise and fall in cavity pressure variations get stabilized at the desired preset value within a fraction of seconds. Alternatively if the cavity expands a suitable volume of fluid is sucked into the cavity from the irrigation circuit, such as from the region of point 6, and this is accompanied by a corresponding transient decrease in the flow rate at which fluid is escaping via the constriction site 8 in the direction of point 3 but if the magnitude of the said physiological expansion is more fluid may even be sucked into the cavity via the constriction site 8. This implies that the constriction site 8 is helping in maintaining a stable cavity pressure despite physiological cavity wall contractions by suitably varying the magnitude of an imaginary fluid flow vector passing through the constriction site 8. Normally the direction of such imaginary vector is always towards point 6 while its magnitude constantly varies to take care of the pressure changes resulting due to physiological cavity contractions. Normally a cavity continuously contracts and dilates by approximately the same magnitudes thus there is no logic to check the minor pressure variations emanating from the said contractions. Also the opening of the constriction site 8 does not allow the said physiological cavity pressure fluctuations to cause any significant cavity wall movement excursions by allowing to and fro movement of flow through its lumen. However, if the said pressure changes are made to be corrected by a controller, as is done in the prior art systems, the cavity wall may exhibit significant irregular pressure fluctuations which may result in significant movement excursions of the cavity wall, thus disallowing a predictably stable mechanical stabilization of the cavity walls. However, in the eventuality of fluid intravasation the fall in cavity pressure drop is relatively more permanent in nature thus needs to be corrected by the controller. As explained in the previous paragraph the controller is so programmed that the inflow pump 4 automatically comes under the pressure feedback control mechanism of the controller in case the cavity pressure alters by a desired minimum preset magnitude and for a desired preset time interval, thus a new ‘R1.Final’ inflow rate is established at which the inflow pump is again allowed to operate without the feedback control of the controller. As a safety precaution a provision can be made in the controller via suitable input means to fix an upper safe limit for the inflow rate R1 and the cavity pressure P such that these safe limits are not exceeded accidentally.

Removing the Outflow Pump

Referring to FIG. 2 the outflow pump 14 can also be totally removed and the outflow tube 12 may be made to drain directly into the waste fluid container 16. In such a case a permanent constriction can also be incorporated inside the out flow tube 12. A vacuum source can also be attached to the waste fluid collecting container 16. However the embodiment described in this paragraph is much inferior to the system of the proposed invention and it is for this reason that schematic diagrams related to this inferior embodiment have not been included in this manuscript.

A Variable Constriction Site

In context with the system shown in FIG. 2 it is also possible to have a system in which the cavity pressure is maintained and regulated by continuously varying, by the help of a controller, the diameter D at the constriction site 8. The housing tube having the constriction site is substantially responsible for dampening the pressure pulsation or minimizing the turbulence inside the cavity. It however may not provide any substantial dampening to the pressure pulsation caused by the working of the inflow or outflow pumps. The diameter D at the constriction site 8 could also be intermittently regulated by a controller as and when required for example in the eventuality of fluid intravasation or extravasation thus implying that the diameter D shall be free from the influence of the controller for most of the time and shall be brought under the influence of the controller only when needed and that also for only a small part of the total surgical time. Such a concept has been described in great detail in the previous paragraphs in context with FIG. 2. In the variable constriction system proposed in this paragraph both pumps 5 and 14 would always operate at desired but fixed flow rates and the cavity pressure would be regulated only by varying the diameter D at the constriction site 8. At the start of the surgery the inflow and outflow rates would be set by feeding suitable flow rate values into the controller after which the controller would not influence or regulate the said two pumps and the cavity pressure would be maintained only by varying the diameter D at the constriction site 8. In order to vary the diameter at the constriction site 8 a suitable electromechanical devise such as a solenoid operated devise could be installed over the housing tube 7. Such a devise is not a devise which would either totally close or totally open the lumen of the pipe. By the help of the said devise the lumen diameter would be varied in a controlled manner and not just by totally opening or totally closing the lumen. The said devise could comprise of a long coil containing a movable long cylindrical magnet and this magnet piece by pressing over the tube, would vary the inner diameter of the tube. When current passes through such coil the magnet piece would either be pulled in or pushed out depending upon the direction of the current and the polarity of the magnet and the force which the said long cylindrical magnet piece could apply over the plastic tube would depend upon the current density passing through the coil or in simpler terms the amount of electrical energy supplied to the coil. In context with the present paragraph the controller shall regulated the amount of electrical energy supplied to the coil such that the magnetic rod presses over the tube with an adequate force and the inner diameter of the pipe would depend upon such force. Thus the inner diameter of the tube shall be a function of the current density. The system efficiency of this particular embodiment of the proposed invention could be greatly enhanced by incorporating a system of pump synchronization as described in the next paragraph. The variable constriction site as described in this paragraph has not been included in any of the figures only to keep the manuscript simple.

A System of Pump Synchronization

As discussed in the preceding paragraphs the system of the proposed invention as shown in FIGS. 2 and 3 helps in considerably reducing cavity fluid turbulence. However the two perictaltic pumps create pressure pulsations which in turn causes some turbulence inside the cavity. A method shall now be described to minimize such turbulence by synchronizing the two peristaltic pumps on a single common central shaft. The two positive displacement inflow and outflow pumps 5 and 14, which are preferably peristaltic pumps, can be attached, that is mounted, on a common central driving shaft which is in turn rotated by a common single motor. Referring to FIG. 7, the two peristaltic pumps 5 and 14 are mechanically coupled to a common driving shaft 26 which is driven by the motor 35. The motor 35 can be any suitable motor for example a DC electric motor. Points 27 and 28 refer to the mechanical coupling sites between the common driving shaft 26 and the pumps 5 and 14. In FIG. 7 the rollers of the peristaltic pump 5 have been referred to as 20, 22 and 24 and the symbolic attachment of these rollers with the central axis point 27 is denoted by lines 29, 30 and 31 respectively. The rollers of the peristaltic pump 14 have been referred to as 21, 23 and 25 and the symbolic attachment of these rollers with the central axis point 28 is denoted by lines 32, 33 and 34 respectively. The inner diameter of tube 4 related to the inflow peristaltic pump 5 has to be greater than the inner diameter of tube 13 related to the outflow pump 14 and the same had also been diagrammatically depicted in FIG. 7. The motor 35 rotates the common driving shaft 26 in the direction of the curved arrow located at the extreme right side of the diagram in FIG. 10. The common driving shaft 26 being mechanically coupled to the two peristaltic pumps, rotates these pumps in the direction of the two curved arrows related to each pump. In FIG. 7 the rollers of the two peristaltic pumps are seen located at 12 'O clock, 4 'O clock and 8 'O clock positions respectively for both pumps. Let us consider rollers 20 and 25 related to the inflow and the outflow pumps respectively. Let it be assumed that when the motor 35 rotates the diving shaft 26 then it takes a time T for the roller 20 of the inflow pump 5 to move from its initial 12 'O clock position to 4 'O clock position. Let it also be assumed the outlet end of the inflow pump 5 to be situated at 4 'O clock position. As the two pumps are mechanically coupled to the common shaft 26 the corresponding roller 25, related to the outflow pump 14 also takes the same time T to move from its initial 8 'O clock position to the 12 'O clock position. Let it also be assumed the inlet end of the outflow pump 14 is located at the 8 'O clock position. While the roller 20 moves from the 12 'O clock position to the 4'O clock position a positive pulse having a magnitude M1 tends to be created inside the tissue cavity. While the roller 25 moves from the 8 'O clock position to the 12 'O clock position a negative pressure pulse having a magnitude M2 tends to be created inside the tissue cavity. As the two peristaltic pumps are synchronized the said positive and negative pressure pulses having magnitudes M1 and M2 tend to cancel or negate the effect of each other and the magnitude M3 of the resultant pressure pulse is equal to M1−M2. The magnitude of the resultant pressure pulse can be made almost negligible by suitable mechanical adjustments of the spatial alignment of the rollers of the two peristaltic pumps. The roller 20 related to the inflow pump and the roller 25 related to the outflow pump have been termed as ‘corresponding rollers’ because while roller 20 of the inflow pump creates a positive pressure pulse inside the cavity by pushing fluid into the cavity the roller 25 creates a negative pressure pulse inside the cavity by actively extracting fluid out of the cavity. A similar example can also be proposed for corresponding rollers 24 and 23, and rollers 22 and 21. In the system shown in FIG. 10 the spatial alignment of rollers related to both the pumps can be adjusted experimentally in order to achieve the minimal possible fluid turbulence and once the minimum desired turbulence level is achieved the relative orientation or alignment of the corresponding rollers is not changed. It is clear that the magnitude of the said ‘net pressure pulse’ depends upon M2, M3 and the relative instantaneous spatial position of the said corresponding rollers. If the inflow and the outflow pumps are not synchronized via the common shaft 26 or if the pumps run at different RPM's the M1 and M2 can never cancel or negate the effect of each other thus leading to fluid turbulence. Thus by synchronizing the two peristaltic pumps via the common driving shaft 26 the fluid flow through the cavity can be made almost pulseless and very close to laminar or a streamline flow.

Thus by synchronizing the two pumps cavity fluid turbulence can minimized or almost negated. If the two pumps rotate at different RPM's then the relative corresponding positions of the rollers of the two pumps constantly keeps on changing which gives rise to unwanted cavity fluid turbulence. However in the ‘synchronized pump system’ described in this paragraph the flow rates of the inflow and the outflow pumps cannot be altered independent of each other and if the cavity pressure needs to be varied without changing pump RPM's then the same is possible only varying the diameter D of the constriction site 8.

A Method to Dampen the Pressure Pulsations of a Peristaltic Pump

The ‘system of pump synchronization’ discussed in the previous paragraphs helps in reducing or dampening the pressure pulsations created by the two peristaltic pumps thereby it helps in reducing the turbulence inside the tissue cavity. However such system of attaching the two peristaltic pumps on a single common driving shaft is practically difficult and it does not allow the two pumps to be run independently of each other thus an easier method of dampening the pressure pulsation of a peristaltic pump is being proposed and the same shall henceforth be referred to as ‘pressure pulse dampening system’ while the other method is being termed as ‘pump synchronization system’.

Referring to FIG. 4 the fluid pressure, such as at a point 6, is pulsatile in nature because the peristaltic pump 5 constantly pushes fluid via its outlet end in the form of a pulsed manner and not in a continuous manner. Hypothetically assuming that the pump 5 rotates at fixed RPM then in that case the frequency of such pulsations would remain uniformly the same all through the operation of the pump. If a graph is plotted for the said pulsations, by relating the fluid pressure to the ‘Y’ axis and the time to the ‘X’ axis, then such graph would have a uniform shape having positive and negative pressure swings of a predictably fixed amplitude and fixed frequency. It is to be noted that as the pump RPM is increased the frequency as well as the amplitude of the said pressure swings also increase. The said pulsations are produced because each time any one roller of the peristaltic pump comes in apposition with a fixed point, for example the outlet end of the peristaltic pump, some fluid is pushed out from the outlet end of the pump in the form of a bolus. The wave form of such pulsations need not be sinusoidal, but for the sake of an easier understanding let the said waveform be hypothetically assumed to be sinusoidal in nature. As already stated, if the pump RPM increase then along with the frequency the amplitude of the said waveform also increases. When the pump 5 rotates in the direction of the curved arrow fluid tends to accumulate in tube 9 and in tube 7 between points 6 and 8, and let this cavity consisting of tube 9 and the said part of tube 7, into which the fluid tends to accumulate, be termed as ‘fluid accumulation region’. In physical terms the said pressure pulsations are produced because the fluid tends to accumulate in the ‘fluid accumulation region’ in the form of regular pulses wherein each pulse corresponds to a fixed volume of fluid pushed by a roller into the ‘fluid accumulation region’ in the form of a bolus of fluid. Thus the motion of each roller would correspond to one complete sinusoidal pressure wave. The movement of a single roller in relation to a fixed point such as the outlet end of the pump can be hypothetically divided into three parts, that is, part one when the roller approaches the said point, part 2 when the roller is in apposition with the said point and part 3 when the roller moves away from the said point. Let the parts 1, 2 and 3 be collectively termed as ‘single roller movement’ and the time taken to accomplish the said ‘single roller movement’ be termed as ‘single roller time’. Assuming the pressure waveform to be a sinusoidal curve, each ‘single roller movement’ corresponds to one complete sinusoidal pressure waveform consisting of a positive pressure surge followed by a negative pressure surge or vice versa. Also the time period of the assumed sinusoidal wave form would be equal to ‘single roller time’. If during the positive pressure surge an adequate volume of fluid is removed from the ‘fluid accumulation region’ and during the negative pressure surge the same adequate volume of fluid is again added back into the ‘fluid accumulation region’ the sinusoidal nature of the pressure waveform could get dampened and the resultant waveform would get transformed into an almost straight line curve. The resultant waveform could theoretically be an absolute straight line if the wave form associated with the said process of adding and removing adequate volumes of fluid from the ‘fluid accumulation region’ absolutely resembled with the wave produced as a result of the pulsatile flow of the peristaltic pump and the phase difference between the two waves was exactly 180 degrees however this may not be achieved in practical situations. However a substantial dampening of the resultant waveform could be practically achieved if a syringe system was synchronously coupled with the inflow peristaltic pump 5 and the single outlet end of the said syringe system was connected with the ‘fluid accumulation region’. Referring to FIG. 8, this figure is the same as FIG. 4 except that a said syringe system 38 has been included. The syringe system 38 consists of a piston 39 denoted by a shaded area. The piston 39 moves up and down inside a cylinder 43 while making a watertight contact with the inner walls of this cylinder 43. One end of a straight rod 40 is connected to the piston while the other end of this rod 40 is connected to a coupling mechanism 37 housed on a common shaft 36. The coupling mechanism 37 and the peristaltic pump 5, both are attached on to a common shaft 36. The coupling mechanism 37 is so designed that it converts the rotary motion of the shaft 36 into a linear up down motion of rod 40 which is ultimately manifested as an up down movement of piston 39 inside the cylinder 43. The up down motion of the rod 40 is denoted by arrows 41 and 42. Thus the shaft 36 is a common shaft which mechanically operates both, pump 5 as well as the syringe system 38. The direction of rotation of the shaft 36 is denoted by a curved arrow located at the right end of the shaft 36. The syringe system 38, as the name suggests, resembles a hypodermic syringe used for giving injections to patients. Obviously, the syringe system 38 has only one single opening 44. A tube 45 extending between the opening 44 and the inflow tube 10 connects the syringe system to the inflow tube 10. Tube 10 is a part of the said ‘fluid accumulation region’ described in this paragraph. Thus the syringe system can be considered to be connected with the said ‘fluid accumulation region’. The opening 44 can be referred to as an ‘outlet end’ or an ‘inlet end’ because the syringe system can push as well as pull fluid from the ‘fluid accumulation region’. However for the sake of convenience henceforth the opening 44 shall be termed as the outlet end of the syringe system 38. The coupling mechanism 37 is so designed that the vertical movements of the syringe system can be accurately synchronized with the rotary motion of the peristaltic pump 5. The piston 39 can move up>down>up or down>up>down, depending upon the initial position of the piston at the start of the motion and let each such movement of the piston be termed as a ‘complete piston movement’. The coupling mechanism 37 is so designed that while the peristaltic pump 5 rotates by 360 degrees the syringe system correspondingly exhibits ‘complete piston movements’ which are equal to the number of the rollers of the peristaltic pump. Thus for a peristaltic pump which has three rollers then for each 360 degrees rotation of the peristaltic pump the syringe system exhibits three ‘complete piston movements’ while for a peristaltic pump with four rollers four ‘complete piston movements’ would occur for each 360 degree rotation of the peristaltic pump. The syringe system is synchronized with the peristaltic pump via the coupling mechanism 37 in such manner that while a roller of the peristaltic pump produces a positive pressure pulse the syringe system extracts fluid out from the ‘fluid accumulation region’ and while the same roller produces a negative pressure pulse the syringe system pushes an equivalent volume of fluid back into the ‘fluid accumulation region’. In order to dampen the pulsations of the peristaltic pump, besides mechanically synchronizing the syringe system with the peristaltic pump the volume of fluid pulled in or pushed out of the syringe system corresponding to each upward or downward movement of the piston also has to be adjusted accurately, and the same may be done manually by a ‘hit and try method’. The volume of fluid pulled in or pushed out by the syringe system depends upon the linear movement excursion of the piston 39. Also the magnitude of the downward piston excursion is equal to the magnitude of the upward piston excursion, thus the volume of fluid pushed out is always equal to the volume of fluid pulled in during each downward or upward movement. Thus the coupling mechanism 37 has two functions, synchronization of the syringe system with the peristaltic pump and adjusting the volume of fluid pulled in or pushed out by the syringe system for each upward or downward movement of the piston. The synchronization and the determination of the said volume to be pushed out or pulled into the syringe system are done manually such that a substantial dampening of the pressure pulsations is achieved and once this is achieved the synchronization at the level of the coupling 37 is never again disturbed and the volume of fluid pulled in or pushed out of the syringe system for each movement excursion is also not changed thereafter. After the coupling 37 is adjusted with respect to synchronization and the volume of fluid to be pulled in and pushed out, the peristaltic pump pulsations shall continue to remain dampened independent of the peristaltic pump RPM and the nature of rotation, that is fixed or variable RPM. In simpler terms the peristaltic pump pulsations would continue to remain dampened even at a high pump RPM. Also the point at which the syringe system 38 is connected to the said ‘fluid accumulation region’, for example the inflow tube 10, then the position of such a point should also not be changed thereafter because this may bring about a phase difference between the waveform related to the peristaltic pump pulsations and the waveform related to the syringe system pulsations, thus the resultant dampening could no longer be satisfactory. Also preferably the outlet tube 45 of the syringe system should be connected as close to the outlet end of the inflow peristaltic pump as possible.

The coupling 37 can be compared to some extent with the conventional CAM system present in automobile engines. Any specific mechanical design for the coupling 37 is not important, it is the resultant function of the coupling 37 with respect to the piston movement, as already described, which is important. The coupling 37 can have many mechanical designs. FIG. 9 shows one such possible mechanical design for the coupling 37. In FIG. 9 a small length of the common shaft 36, which is related to the coupling 37, has been made of triangular shape as seen in its cross sectional view and the same is labeled as 49. Let this triangular part 49 be termed as the ‘piston coupler’. The edges of the piston coupler are shown sharp however they could preferably be rounded to suit various operational needs. Similarly the size of the ‘piston coupler’ could also be increased or decreased in order to decrease or increase the volume of fluid displaced by the cylinder during a downward or upward movement of the piston. The central axis point of the ‘piston coupler’ is denoted by point 48. In case the dimensions of the ‘piston coupler’ are chosen to be relatively larger than the dimension of the common shaft 36, the point 48 could also represent the point at which the common shaft 36 passes through the ‘piston coupler’ and in such a situation the ‘piston coupler’ 49 could be manually rotated on the common shaft 36 in a clockwise or anti clockwise direction and then locked mechanically at a position which provides the most accurate synchronization. The springs 46 and 47 extending between the inner walls of the cylinder and the piston exert a constant and substantially large upward pull on the piston 39 which causes the rod 40 to constantly be in apposition with the ‘piston coupler’ 49. The springs can be one or more than one in number and the springs can also be substituted by any other mechanical means also which provide an active upward movement of the piston. The ‘piston coupler’ 49 is assumed to be able to apply a substantially large downward force on the piston 39 via rod 40 such that a corresponding transient negative fluid pressure pulse inside the cylinder can be totally neglected in the face of the said large substantial downward force. Similarly the springs 46 and 47 are capable of pulling up the piston with a substantially large force such that a corresponding transient positive fluid pressure pulse inside the cylinder could be totally neglected. The idea is that the downward movement of the piston should not be aided by the negative pressure pulse inside the cylinder, this downward movement should be an active movement for which energy is to be derived from the springs from the shaft 36. Similarly the upward movement of the piston should not be aided by the positive pressure pulse inside the cylinder, this upward movement should be an active movement for which energy is to be derived from the springs 46 and 47. The energy for the said upward movement of the piston could also be derived from the shaft 36 if suitable mechanical provision facilitating an active upward movement of the piston could be provided at the level of the coupling 37.

It is important to note that it is not mandatory to use the said ‘pressure pulse dampening system’ with a peristaltic pump only as, with suitable mechanical modifications, the ‘pressure pulse dampening system’ could be used beneficially with any type of a positive displacement pump.

The ‘pressure pulse dampening system’ could also be a mechanism like the ‘piston coupler’ shown in FIG. 9 whose rounded edges could directly impinge on a suitable area situated on the outer surface of the ‘fluid accumulation region’ in a uniform synchronized manner, as described, such that this results in continuous uniform synchronized variations in the total volume capacity of ‘fluid accumulation region’. The said suitable area on the outer surface of the ‘fluid accumulation region’ could be a membrane made consisting of a strong resilient polymeric material having an adequate elasticity. The said membrane should also be sufficiently thick and should have an adequate elasticity such that an outward movement of such membrane, a movement related to the upward pull by the said springs, applied a substantially larger force in comparison to force related with the transient corresponding pressure pulse.

A ‘pressure pulse dampening system’ presently being described for the inflow pump 5 should be preferably installed on the outflow peristaltic pump 14 also in an exactly similar manner as already described. Thus the said dampening is possible for both, inflow and outflow pumps or for only one single pump, the inflow or outflow one. Obviously the overall effect of the said dampening as perceived inside the tissue cavity 18 shall be more if the said dampening is done at the level of both the pumps because the pressure pulsations from both pumps travel to the tissue cavity 18 and thus they need to be dampened at the level of both pumps. It is also to be noted that ‘pressure pulse dampening system’ is different from the ‘pump synchronization’ system accomplished by housing the two peristaltic pumps on to a single common shaft, while in the ‘pressure pulse dampening system’ both the peristaltic pumps are housed on separate shafts. ‘Pump synchronization’ is more difficult to achieve when compared to the ‘pressure pulse dampening system’, however the two methods can also be utilized simultaneously but in that case both the peristaltic pumps shall have to be attached on to the same common driving shaft.

In FIG. 1 the inflow 38 and the outflow 55 syringe systems have been shown synchronized with the inflow and outflow peristaltic pumps 5 and 14 respectively. In the outflow syringe mechanism the common shaft houses the coupling 51 which moves the piston 54 via shaft 63 inside the cylinder 64 whose outlet opening 56 is connected to the outflow tube 12 via tube 57. The coupling system shown in FIG. 9 would be applicable to this outflow syringe system also.

The pressure dampening mechanism described in the present invention is an active pressure dampening system and not a passive dampening system. The Applicants have realized that only active pressure dampening systems as discussed above provide substantial dampening to the pressure pulsation caused by the peristaltic pumps and relying on passive factors such as the inherent resistance to the flow of the liquid etc do not provide any effective pressure dampening. Further, the pressure dampening system may not provide any substantial dampening to the pressure pulsation caused by the physiological contractions of the cavity walls.

A System of Incorporating Multiple Peristaltic Pump Tubes

In the preceding parts of the manuscript the two peristaltic pumps 5 and 14 are shown to have one single tube each, that is tubes 4 and 13 respectively, which come in contact with the rollers of the peristaltic pumps. Arbitrarily referring to the inflow pump 5,

${R\; 2} = {\frac{\pi\; \times B^{2} \times L}{4} \times {RPM} \times 2}$ where R2=Flow rate of pump 5, B=inner diameter of the peristaltic pump tube 4, L=length of tube 4 and RPM=revolution per minute of pump 5. If the value B is doubled then for the same RPM the flow rate R2 doubles. Similarly if L doubles then also for RPM the flow rate R1R2 doubles. However keeping in mind the mechanical constraints the values B and L cannot exceed a certain practical value. However if two tubes like tube 4 are used in parallel in the pump 5 then the mathematical expression for the flow rate could be written as follows:

${R\; 2} = {\frac{\pi \times B^{2} \times L}{4} \times {RPM}}$ This implies that if two peristaltic pump tubes are used instead of one single tube then the flow rate becomes double for the same RPM and if three tubes are used then the flow rate becomes three times and so on. The frequency of the ‘pressure pulsations’ created by a peristaltic pump is directly proportional to the pump RPM. The said ‘pressure pulsations’ are undesirable thus it is helpful to keep their frequency as minimal as possible if the flow rate is not compromised. Thus this system of incorporating two or more peristaltic pump tubes helps in attaining a higher flow rate for a relatively lesser RPM. It is but obvious that the said two or more than two parallel tubes are connected to each other at the inlet and the outlet ends of the peristaltic pump. Determination of the Instantaneous Real Time Rate of Fluid Intravasation

Fluid intravasation is a process by which the irrigation fluid enters into the patient's body system and if excess volume of fluid is intravasated it can be dangerous to the patient's life. Thus, keeping in mind surgical safety, it is extremely important to constantly know the rate at which such intravasation occurs so that corrective surgical measures can be taken before a dangerous volume of fluid intravasates. The inventors propose that one fluid flow rate sensor each be incorporated in the inflow tube and the outflow tube. Referring to FIGS. 1, 2 and 3 the inflow flow rate sensor should be located in the inflow tube 10 anywhere between the inlet port of the endoscope and the point at which the distal end of the constriction site housing tube 7 is connected to the inflow tube, such as point 6. Such a flow rate sensor would measure the rate at which fluid enters into the tissue cavity 18 and the same is being termed as ‘cavity inflow rate’. Obviously the ‘cavity inflow rate’ is the true inflow rate for the tissue cavity. Similarly the outflow flow rate sensor should be located anywhere in the out flow tube between the outflow port of the endoscope and the inlet end of the outflow peristaltic pump 14 or any other outflow positive displacement pump. However if an additional or optional constriction site housing tube 117 is also connected to the out flow tube 12 as shown in FIG. 6 then the outflow flow rate sensor should be located between the outflow port of the endoscope and the point at which the proximal end of the constriction site housing tube 117 is connected to the outflow tube 12. The outflow flow rate sensor measures the rate at which fluid is extracted from the tissue cavity which is the same as R2 that is the flow rate of the outflow pump. Now the real time rate of fluid intravasation, being termed as R3, can be determining by subtracting R2 from the ‘cavity inflow rate’, the mathematical expression for the same being can be written as R3=Cavity inflow rate−R2. The said flow rate sensors should be accurate, reliable, easy to install and should not have any movable parts. The inventors suggest that said sensor comprise of a heating coil in physical contact with a metal plate for heating the same and a temperature sensor placed in contact with the metal plate, the temperature of the metal plate being a function of the fluid flow rate. The said flow rate sensors are electrically connected with a micro-controller which automatically subtracts R2 from the ‘cavity inflow rate’ to give the value R3. The value R3 can also be further integrated with respect to time to give the total volume of fluid intravasated over a certain time interval. The said temperature related flow rate sensor could be a ‘hot wire anemometer’.

The proposed invention can also be used to impart endoscopic training skills by the help of endoscopic experimental models based on the present invention. Also use and scope of the present invention is not limited to human tissue cavities and it may be used for performing multiple endoscopic procedures in animal tissue cavities also and also for imparting training in endoscopic surgeries related to animal tissue cavities.

It is believed that the foregoing description conveys the best understanding of the objects and the advantages of the present invention. It will be understood by those skilled in the art that numerous improvements and modifications may be made to the embodiments of the invention disclosed herein without departing from the departing from the spirit and scope thereof.

The Invention is Unique

There is no other prior art system in which the amplitude of pressure pulsations produced by a positive displacement, like a peristaltic pump, could be minimized to a negligible level. Also the concepts of ‘pressure pulse dampening system’, ‘system of pump synchronization’, determination of the instantaneous rate of fluid intravasation by using two hot wire anemometers and the concept of installing two or more peristaltic tubes in parallel have not been described in any prior art system

The Heart and Soul of the Invention

The ‘pressure pulse dampening system’ using a syringe mechanism is the heart and soul of the invention without which the invention cannot exist.

Advantages of the Proposed Invention

The proposed invention makes endoscopic procedures extremely safe, simple, more accurate and easy to perform. The proposed invention helps the surgeons to perform endoscopic surgeries with greater safety and confidence especially in the initial phase of their learning curve. Also a distending system based on the proposed invention can be used in multiple endoscopic procedures thus reducing the financial burden on the hospital and the patient. The advantages of proposed invention are summarized in the following table along with the corresponding disadvantages of the prior art systems:

ADVANTAGES OF THE DISADVANTAGES OF THE PRESENT INVENTION: PRIOR ART SYSTEMS: It is possible to reduce the This is not possible in amplitude of the pressure pulsations any prior art system. created by a positive displacement pump to an almost negligible magni- tude irrespective of the pump RPM. It is possible to minimize cavity This is not possible in fluid turbulence to almost negligible any prior art system. levels. It is possible to create and maintain This is not possible in any desired precise tissue cavity any prior art system. pressure for any desired precise fixed outflow rate including a zero outflow rate. The instantaneous real time rate of Such feature is not fluid intravasation into the patient's present in any prior body is constantly known by using a art system. hot wire anemometer type of a flow rate sensor. The instantaneous real time rate of This is not possible in fluid intravasation into the patient's any prior art system. body can be determined even mechanically without using a controller and any type of fluid flow rate sensors. A predictably constant any desired This is not possible in fluid pressure can be maintained any prior art system. inside a tissue cavity for indefinite time. A predictably constant any desired This is not possible in fluid pressure can be maintained any prior art system. inside a tissue cavity for indefinite time despite physiological cavity wall contractions. A predictably constant clear This is not possible in endoscopic visualization is possible. any prior art system. It is possible to achieve a This is not possible in predictably stable mechanical any prior art system. distension of the cavity walls. It is possible to maintain any desired This is not possible in precise and high cavity pressure any prior art system. without increasing the ‘maximum possible fluid intravasation rate’. It is possible to easily and quickly This is not possible in change over from one type of any prior art system. irrigation fluid to a different type of irrigation fluid during an endoscopic procedure in any desired short period of time such that the cavity pressure does not change during such maneuver. Conclusion

The proposed invention is novel and unique. The invention relates not only to increasing surgical efficiency in certain endoscopic procedures but it also helps in preventing human morbidity and human mortality in many endoscopic procedures. Thus the proposed invention is extremely useful for entire mankind. 

We claim:
 1. A system for distending body tissue cavities of subjects by continuous flow irrigation during endoscopic procedures, the system comprising: a fluid source reservoir containing a non viscous physiologic fluid; a fluid supply conduit tube connecting the fluid source reservoir to an inlet end of a positive displacement inflow pump and an outlet end of the inflow pump being connectable to an inflow tube for pumping the fluid at a controlled flow rate into the cavity, the flow rate at which the fluid enters into the cavity via the inflow tube being termed as the cavity inflow rate; an inflow pressure pulsation dampening means connected to the inflow tube for dampening the pressure pulsations inside the cavity created by the positive displacement inflow pump; an outflow tube connectable to an inlet end of a positive displacement outflow pump for removing the fluid from the cavity at a controlled flow rate, the flow rate of the outflow pump being termed as the cavity outflow rate; an outflow pressure pulsation dampening means connected to the outflow tube for dampening the pressure pulsations inside the cavity created by the positive displacement outflow pump; an outlet end of the outflow pump connected to a waste fluid collecting container; and a tube having a fixed constriction site provided between the fluid source reservoir and the inflow tube such that the same by-passes the inflow pump, the constriction site having fixed diameter, wherein tube provides a route for any excess fluid being pumped by the inflow pump to bypass the inflow pump.
 2. The system as claimed in claim 1, wherein a proximal open end of the fluid supply tube is connected to the fluid source reservoir and a distal end of the tube is connected to the inlet end of the positive displacement inflow pump.
 3. The system as claimed in claim 2, wherein the proximal open end of the fluid supply tube is constantly and completely immersed in the fluid source reservoir.
 4. The system as claimed in claim 1, wherein a proximal end of the inflow tube is connected to the outlet end of the positive displacement inflow pump.
 5. The system as claimed in claim 1, wherein the positive displacement inflow pump is selected from the group consisting of peristaltic pump, piston pump, gear pump, diaphragm pump and plunger pump.
 6. The system as claimed in claim 5, wherein the positive displacement inflow pump is a peristaltic pump.
 7. The system as claimed in claim 1, wherein the tube is releasably provided between the fluid source reservoir and the inflow tube to enable replacement of the tube with another housing tube having a different diameter at the constriction site to suit the operational need of the endoscopic procedure.
 8. The system as claimed in claim 1, wherein a proximal end of the tube is connected to the fluid supply tube near its distal end close to the inlet port of the inflow pump.
 9. The system as claimed in claim 1, wherein a proximal end of the tube empties directly into the fluid source reservoir and is constantly and completely immersed in the fluid source reservoir.
 10. The system as claimed in claim 1, wherein a distal end of the tube is connected to the inflow tube near its proximal end close to the outlet end of the inflow pump.
 11. The system as claimed in claim 1, wherein the tube is provided with a clamping means at the constriction site to enable the user to vary the diameter of the tube at the constriction site to suit the operational needs of endoscopic procedures.
 12. The system as claimed in claim 1, wherein the diameter of the tube at the constriction site is in the range of 0.001 mm to a maximum value which is less than the overall diameter of the rest of the tube.
 13. The system as claimed in claim 1, wherein the diameter of the tube at the constriction site is in the range of 0.01 to 2.5 mm.
 14. The system as claimed in claim 1, further comprising an inflow pressure transducer located away from the cavity site, near the outlet end of the inflow pump, such that the fluid pressure measured by the same is almost equal to the fluid pressure inside the cavity.
 15. The system as claimed in claim 1, wherein a proximal end of the outflow tube connectable to the outlet port and a distal end of the outflow tube is connected to an inlet end of the positive displacement outflow pump.
 16. The system as claimed in claim 1, further comprising an outflow pressure transducer connected between the proximal end of the outflow tube and the inlet end of the positive displacement outflow pump for measuring the pressure in the outflow tube.
 17. The system as claimed in claim 1, wherein the positive displacement outflow pump is selected from the group consisting peristaltic pump, piston pump, gear pump, diaphragm pump and plunger pump.
 18. The system as claimed in claim 17, wherein the positive displacement outflow pump is a peristaltic pump.
 19. The system as claimed in claim 1, wherein the outlet end of the positive displacement outflow pump is connected to the waste fluid collecting container through a waste fluid carrying tube.
 20. The system as claimed in claim 1, further comprising a micro-controller electrically coupled to an inflow pressure transducer, an outflow pressure transducer, the inflow pump and the outflow pump for regulating the operation of the inflow and the outflow pumps.
 21. The system as claimed in claim 1, further comprising another tube having a variable size constriction site being provided between the outflow tube and the waste fluid reservoir.
 22. The system as claimed in claim 21, wherein the distal end of the another tube is connected to the outflow tube.
 23. The system as claimed in claim 1, wherein the fluid supply tube, the inflow tube, and the outflow tube are flexible, disposable and are made of polymeric material.
 24. The system as claimed in claim 1, wherein the inflow and the outflow positive displacement pumps are coupled to a common shaft for synchronously operating the inflow and the outflow positive displacement pumps.
 25. The system as claimed in claim 24, wherein the tube is provided with an electromechanical device to enable the micro-controller to vary the diameter of the constriction site.
 26. The system as claimed in claim 24, wherein if the inflow and the outflow pumps are coupled to the common shaft, the tube is essentially provided with the micro-controller controller for varying the diameter of the constriction site.
 27. The system as claimed in claim 6, wherein the inflow and outflow peristaltic pumps are provided with 1 to 5 peristaltic pump tubes connected in parallel between the inflow and outflow ends of the peristaltic pumps for reducing the frequency of pulsations in the pressure, the tubes being connected to each other at the inflow and outflow ends of the peristaltic pumps, and the peristaltic pump tubes contacting rollers of the peristaltic pumps.
 28. The system as claimed in claim 1, wherein the inflow pressure pulsation dampening means comprises a single outlet syringe, the piston of the same being coupled to the positive displacement inflow pump in a synchronous manner through a coupling means such that movement of the piston is not influenced by the fluid pressure at the inlet end of the inflow pump and a single outlet end of the syringe mechanism being connected to the inflow tube.
 29. The system as claimed in claim 1, wherein the outflow pressure pulsation dampening means comprises a single outlet syringe, the piston of the same being coupled to the positive displacement outflow pump in a synchronous manner through a coupling means such that movement of the piston is not influenced by the fluid pressure at the inlet end of the outflow pump and a single outlet end of the syringe mechanism being connected to the outflow tube.
 30. The system as claimed in claim 24, wherein if the inflow and the outflow pumps are operated synchronously by coupling them to the common shaft, the inflow and the outflow pressure pulsation dampening means are optionally operated synchronously by coupling them to the same common shaft.
 31. The system as claimed in claim 1, wherein a first sensor is located in the lumen or wall of the fluid inflow tube for measuring the cavity inflow rate.
 32. The system as claimed in claim 31, wherein the first sensor is located between the inflow pump and a location where the tube is connected to the fluid inflow tube.
 33. The system as claimed in claim 31 further comprising a second sensor between the proximal end of the outflow tube and the inlet port of the positive displacement outflow pump for measuring the cavity outflow rate.
 34. The system as claimed in claim 33, wherein the second sensor is located between the outflow pump and a place proximal to the location where the another tube is connected to the outflow tube.
 35. The system as claimed in claim 31, wherein the first sensor consists of a heating coil in physical contact with a metal plate for heating the same and a temperature sensor placed in contact with the metal plate for measuring the temperature of the metal plate, the temperature of the metal plate being a function of the fluid flow rate.
 36. The system as claimed in claim 31, wherein the first sensor is a hot wire anemometer.
 37. The system as claimed in claim 33, wherein instantaneous real time rate of fluid intravasation is determined by electrically connecting the first and second sensors to a micro-controller.
 38. A system as claimed in claim 1, wherein the fluid source reservoir, the inflow pump, the tubes, the tissue cavity, and the outflow pump are placed approximately at the same height with respect to a horizontal ground. 